US6309354B1 - Non-Invasive in vivo pressure measurement - Google Patents
Non-Invasive in vivo pressure measurement Download PDFInfo
- Publication number
- US6309354B1 US6309354B1 US09/613,648 US61364800A US6309354B1 US 6309354 B1 US6309354 B1 US 6309354B1 US 61364800 A US61364800 A US 61364800A US 6309354 B1 US6309354 B1 US 6309354B1
- Authority
- US
- United States
- Prior art keywords
- pressure
- target region
- blood
- ultrasonic wave
- external pressure
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
- 238000001727 in vivo Methods 0.000 title claims abstract description 13
- 238000009530 blood pressure measurement Methods 0.000 title claims description 7
- 238000000034 method Methods 0.000 claims abstract description 23
- 210000004204 blood vessel Anatomy 0.000 claims abstract description 18
- 239000008280 blood Substances 0.000 claims abstract description 17
- 210000004369 blood Anatomy 0.000 claims abstract description 17
- 239000007788 liquid Substances 0.000 claims description 6
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 4
- 238000004891 communication Methods 0.000 claims description 2
- 230000003993 interaction Effects 0.000 claims description 2
- 238000003825 pressing Methods 0.000 claims description 2
- 230000009466 transformation Effects 0.000 claims 2
- 238000005259 measurement Methods 0.000 abstract description 12
- 230000017531 blood circulation Effects 0.000 abstract description 11
- 238000007917 intracranial administration Methods 0.000 abstract description 8
- 230000005856 abnormality Effects 0.000 abstract description 6
- 230000008859 change Effects 0.000 abstract description 6
- 208000003906 hydrocephalus Diseases 0.000 abstract description 6
- 230000004044 response Effects 0.000 abstract description 5
- 201000010183 Papilledema Diseases 0.000 abstract description 3
- 206010033712 Papilloedema Diseases 0.000 abstract description 3
- 206010038923 Retinopathy Diseases 0.000 abstract description 3
- 201000010099 disease Diseases 0.000 abstract description 3
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 abstract description 3
- 208000017442 Retinal disease Diseases 0.000 abstract description 2
- 230000008081 blood perfusion Effects 0.000 abstract description 2
- 239000002245 particle Substances 0.000 abstract description 2
- 210000000746 body region Anatomy 0.000 abstract 1
- 239000000523 sample Substances 0.000 description 8
- 238000002604 ultrasonography Methods 0.000 description 7
- 230000036772 blood pressure Effects 0.000 description 6
- 239000012530 fluid Substances 0.000 description 5
- 210000004556 brain Anatomy 0.000 description 4
- 230000000694 effects Effects 0.000 description 3
- 230000008569 process Effects 0.000 description 3
- 210000001519 tissue Anatomy 0.000 description 3
- 210000001175 cerebrospinal fluid Anatomy 0.000 description 2
- 201000009941 intracranial hypertension Diseases 0.000 description 2
- 210000001525 retina Anatomy 0.000 description 2
- 208000010412 Glaucoma Diseases 0.000 description 1
- 206010018985 Haemorrhage intracranial Diseases 0.000 description 1
- 208000032843 Hemorrhage Diseases 0.000 description 1
- 208000008574 Intracranial Hemorrhages Diseases 0.000 description 1
- 206010022773 Intracranial pressure increased Diseases 0.000 description 1
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 description 1
- 206010058990 Venous occlusion Diseases 0.000 description 1
- 210000004289 cerebral ventricle Anatomy 0.000 description 1
- 230000001684 chronic effect Effects 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 206010012601 diabetes mellitus Diseases 0.000 description 1
- 210000000744 eyelid Anatomy 0.000 description 1
- 230000000004 hemodynamic effect Effects 0.000 description 1
- 201000001881 impotence Diseases 0.000 description 1
- 230000000149 penetrating effect Effects 0.000 description 1
- 210000004303 peritoneum Anatomy 0.000 description 1
- 230000002028 premature Effects 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 230000000284 resting effect Effects 0.000 description 1
- 210000003625 skull Anatomy 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 210000004127 vitreous body Anatomy 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/06—Measuring blood flow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0048—Detecting, measuring or recording by applying mechanical forces or stimuli
- A61B5/0053—Detecting, measuring or recording by applying mechanical forces or stimuli by applying pressure, e.g. compression, indentation, palpation, grasping, gauging
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
- A61B8/0808—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of the brain
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/04—Measuring blood pressure
Definitions
- the technical field of this invention is medical sonography and, in particular, methods and devices for employing ultrasonic measurements of blood flow to detect and assess diseases or physiological abnormalities.
- cerebrospinal fluid Inside the brain is a ventricular system which contains and conducts cerebrospinal fluid. This cerebrospinal fluid flows through several ventricles within the brain before being absorbed back into the blood. When drainage is blocked, the buildup of fluid results in a pressure which swells the ventricles and increases the pressure throughout the brain. This causes a condition referred to as “hydrocephalus.”
- the intracranial pressure increase associated with hydrocephalus can be relieved surgically by providing a shunt from the ventricle to the peritoneum, this too can frequently result in complications. Accordingly, it is desirable to provide a method and apparatus for reliably measuring the intracranial pressure.
- Intracranial pressure can be measured directly by surgically inserting a pressure transducer inside the cranium.
- a pressure transducer inside the cranium.
- Indirect evidence of intracranial pressure can be obtained by observing the effect of elevated pressure on the structures inside the cranium. For example, one can ultrasonically measure the size of the ventricle and determine whether it is unusually large or whether it has increased in size.
- a hemorrhage either inside the ventricle or in adjacent parenchymal tissue, can obscure the ventricle and make inferences about pressure from observation of its size difficult. Since hydrocephalus is a frequent complication of intracranial hemorrhage in premature infants, this difficulty is frequently encountered in practice.
- An additional disadvantage of the above method is that detectable enlargement of the ventricle requires that the hydrocephalus be chronic. Thus, by the time the elevated intracranial pressure is detected, some damage may have already occurred to the intracranial structures.
- the difficulty in obtaining the intracranial pressure is a manifestation of the more general difficulty of measuring pressure at inaccessible locations within the human body.
- the process of measuring pressure in, for example, a blood vessel involves the application of a mechanical pressure to the vessel itself.
- an inflatable cuff is placed around an arm and inflated until it cuts off the blood flow.
- the cuff pressure required to stop the blood flow provides a measure of the pressure driving that flow.
- the foregoing method of applying a mechanical pressure to a blood vessel is not well suited for the measurement of pressure in specific blood vessels.
- a mechanical pressure to a blood vessel For example, in a diabetic patient afflicted with papilledema, it is often desirable to measure the blood pressure in the capillaries leading to the eye.
- the use of the conventional inflatable cuff to measure blood pressure within the capillaries leading to the retina is made difficult by the lack of a suitable site at which to apply the inflatable cuff.
- the process of inflating the cuff until it cuts off blood flow may be highly intrusive.
- measurement of local blood pressure using a cuff in connection with the treatment of impotence is hardly a practical option.
- An additional disadvantage of the traditional method of measuring blood pressure is that it is unable to detect the rate of change of blood flow as a function of applied pressure. Using the traditional method, one can readily establish the pressure at which blood flow through a vessel ceases. However, one cannot determine, for example, whether the blood velocity began to decrease precipitously at a particular applied pressure or whether it decreased gradually throughout the process of applying an external pressure.
- Apparatus and methods are disclosed for non-invasive measurement of blood velocity in otherwise inaccessible regions, and for correlating such measurements with externally applied pressure to detect and/or assess diseases or physiological abnormalities.
- the blood velocity measurements can be based on the Doppler shift that occurs when an ultrasonic wave is scattered by moving particles within the blood. Since blood vessels have elastic walls, the geometry of the walls, and therefore the flow dynamics, will change in response to elevated in vivo pressure. The change in resistance to blood flow resulting from these pressure induced changes to the wall geometry can provide a measure of intracranial pressure, ophthalmic pressure or various other body conditions that affect blood perfusion. Since wall geometry changes rapidly in response to such changes in pressure, the invention can be used to detect hydrocephalus, glaucoma, retinopathy, papilledema and other physiological abnormalities manifested by pressure changes.
- An apparatus, according to the invention, which uses the change in blood flow to measure the pressure driving that flow includes a pressure applicator containing an acoustically transmitting medium through which ultrasonic waves can propagate between the blood vessel or other intracorporeal fluid and an ultrasonic transducer.
- the pressure applicator is a bladder filled with an acoustically transparent liquid, such as water, and having a deformable side wall which contacts the skin along a contact area.
- the pressure applicator is preferably coupled to a pressure sensor, which measures the pressure applied by the pressure applicator to the surface of the patient, and can be integrated with, or adapted to couple to, an ultrasonic transducer which transmits and receives ultrasonic waves.
- Both the pressure applicator and the ultrasonic transducer are in communication with a data processor which uses the received pressure data and ultrasonic signal in the conventional manner to derive the in vivo pressure of the intracorporeal fluid.
- the invention permits an inferred estimation of in vivo pressure based on the compliance of the target tissue and effect of an externally applied pressure on the hemodynamics in the tissue.
- FIG. 1 is a schematic perspective view of an ultrasound probe and pressure measurement apparatus according to the invention.
- FIG. 2 shows an apparatus according to the invention resting on the skin covering a fontanelle in a neonatal cranium.
- a non-invasive pressure measurement apparatus 10 includes a hand-held ultrasound probe 12 .
- the geometry of the probe 12 is not critical but can be chosen for ease of manipulation.
- Various commercially available ultrasound systems can be used to provide an ultrasound probe 12 and to transmit and receive ultrasonic waves, as well as to provide Doppler shift data.
- U.S. Pat. No. 5,640,960 which is incorporated herein by reference.
- a pressure applicator 13 which includes a housing 15 and a bladder 16 filled with an acoustically transparent medium 18 , is mounted to one end of the ultrasound probe 12 .
- the bladder is a flexible structure which deforms in response to the pressure exerted by it bladder on a surface.
- the acoustically transparent medium can be water, a saline solution, or any other acoustically transparent liquid or gel.
- the pressure applicator 13 preferably includes a pressure transducer 19 which is responsive to the pressure exerted by the bladder on a surface.
- the pressure transducer 19 is coupled to a pressure measurement circuit 22 , the output of which becomes an input to a data processor 24 .
- the pressure applicator 13 can be incorporated into a special purpose ultrasound probe or designed as an adapter which is coupled to a conventional probe.
- An ultrasonic transducer 14 incorporated into the probe 12 converts electronic signals into ultrasonic waves that are transmitted into the medium 18 and, conversely, converts ultrasonic waves returning back from the medium 18 into electrical signals.
- the ultrasonic transducer 14 is electrically coupled to both a waveform generator 21 and a waveform detector 20 .
- the functions of the transducer can be performed by one or more separate transmitters or receivers.
- a housing 15 can surround the bladder 16 to constrain deformation of the bladder when pressure is applied.
- the clinician positions the pressure applicator 13 on the skin over the region in which the blood pressure is to be measured.
- the pressure applicator 13 is shown on the skin 30 covering a fontanelle 36 in a neonatal cranium 32 .
- the clinician applies an external pressure P 1 by pressing a contact surface 17 of the pressure applicator 13 against the skin 30 .
- the pressure thus generated by the operator is transmitted, by way of the fluid within the bladder 16 , to a pressure transducer 19 which generates an electrical signal representative of the applied external pressure for processing by the pressure measurement circuit 22 .
- a pressure regulation 23 can be used to regulate the pressure applied by the bladder's contact surface or to implement an automated or pre-defined protocol of applied pressure. Such a protocol can be initiated or controlled by data processor 24 .
- the apparatus 10 can be placed against a closed eyelid.
- the fluid in the bladder 16 can be acoustically coupled, through the vitreous humor of the eye, to the capillaries feeding the retina for measurement of blood pressure in those capillaries.
- the waveform generator 21 transmits an electrical signal to the transducer 14 which then converts it into an ultrasonic wave.
- the ultrasonic wave propagates through the acoustically transparent medium 18 in the bladder 16 and crosses the skin/bladder interface.
- the fontanelle 36 over which the bladder rests, provides an aperture through which ultrasonic waves crossing the bladder/skin interface can penetrate the cranium 32 and illuminate a blood vessel 34 .
- Ultrasonic waves crossing the bladder/skin interface propagate through the skin 30 and illuminate blood vessels 34 within the brain 38 .
- the interaction of the incident ultrasonic radiation with the blood flow within the blood vessel 34 results in a reflected ultrasonic wave having a frequency shifted by an amount representative of the velocity of the blood within the blood vessel.
- This Doppler shifted ultrasonic wave exits the cranium through the fontanelle 36 , crosses the interface between the skin and the bladder, and propagates through the acoustically transparent medium 18 within the bladder 16 .
- the reflected wave impinges on the ultrasonic transducer 14 and thereby generates an electrical signal representative of the reflected wave. This electrical signal is then transmitted to waveform detector 20 .
- the pressure P 1 applied by the operator against the skin 30 affects the blood velocity in the blood vessel 34 . Since the reflected ultrasonic wave provides a measure of the blood velocity, this wave is likewise affected by the applied external pressure P 1 .
- the measured values of the reflected ultrasonic wave are transmitted to a data processor 24 together with the measured values of external pressure P 1 .
- the data processor 24 uses these two quantities to determine the internal pressure P 2 within the cranium 32 .
Abstract
Apparatus and methods are disclosed for non-invasive measurement of blood velocity in otherwise inaccessible body regions, and for correlating such measurements with externally applied pressure to detect and/or assess diseases or physiological abnormalities. The blood velocity measurements can be based on the Doppler shift that occurs when an ultrasonic wave is scattered by moving particles within the blood. Since blood vessels have elastic walls, the geometry of the walls, and therefore the flow dynamics, will change in response to elevated in vivo pressure. The change in resistance to blood flow resulting from these pressure induced changes to the blood vessel wall geometry can provide a measure of intracranial pressure, ophthalmic pressure or various other body conditions that affect blood perfusion. Since the blood vessel wall geometry changes rapidly in response to such changes in pressure, the invention can be used to detect hydrocephalus, retinopathy, papilledema and other physiological abnormalities manifested by pressure changes.
Description
This application is a continuation of Ser. No. 09/097,067 filed Jun. 12, 1998 now U.S. Pat. No. 6,086,533.
The technical field of this invention is medical sonography and, in particular, methods and devices for employing ultrasonic measurements of blood flow to detect and assess diseases or physiological abnormalities.
Inside the brain is a ventricular system which contains and conducts cerebrospinal fluid. This cerebrospinal fluid flows through several ventricles within the brain before being absorbed back into the blood. When drainage is blocked, the buildup of fluid results in a pressure which swells the ventricles and increases the pressure throughout the brain. This causes a condition referred to as “hydrocephalus.”
Although the intracranial pressure increase associated with hydrocephalus can be relieved surgically by providing a shunt from the ventricle to the peritoneum, this too can frequently result in complications. Accordingly, it is desirable to provide a method and apparatus for reliably measuring the intracranial pressure.
Intracranial pressure can be measured directly by surgically inserting a pressure transducer inside the cranium. However, the inconvenience of surgery and the necessity of penetrating the skull make this method undesirable.
Indirect evidence of intracranial pressure can be obtained by observing the effect of elevated pressure on the structures inside the cranium. For example, one can ultrasonically measure the size of the ventricle and determine whether it is unusually large or whether it has increased in size.
However, a hemorrhage, either inside the ventricle or in adjacent parenchymal tissue, can obscure the ventricle and make inferences about pressure from observation of its size difficult. Since hydrocephalus is a frequent complication of intracranial hemorrhage in premature infants, this difficulty is frequently encountered in practice.
An additional disadvantage of the above method is that detectable enlargement of the ventricle requires that the hydrocephalus be chronic. Thus, by the time the elevated intracranial pressure is detected, some damage may have already occurred to the intracranial structures.
The difficulty in obtaining the intracranial pressure, as described above, is a manifestation of the more general difficulty of measuring pressure at inaccessible locations within the human body. The process of measuring pressure in, for example, a blood vessel, involves the application of a mechanical pressure to the vessel itself. Typically, an inflatable cuff is placed around an arm and inflated until it cuts off the blood flow. The cuff pressure required to stop the blood flow provides a measure of the pressure driving that flow.
The foregoing method of applying a mechanical pressure to a blood vessel is not well suited for the measurement of pressure in specific blood vessels. For example, in a diabetic patient afflicted with papilledema, it is often desirable to measure the blood pressure in the capillaries leading to the eye. The use of the conventional inflatable cuff to measure blood pressure within the capillaries leading to the retina is made difficult by the lack of a suitable site at which to apply the inflatable cuff.
In some cases, even when a suitable pressure application site is available, the process of inflating the cuff until it cuts off blood flow may be highly intrusive. For example, measurement of local blood pressure using a cuff in connection with the treatment of impotence is hardly a practical option.
An additional disadvantage of the traditional method of measuring blood pressure is that it is unable to detect the rate of change of blood flow as a function of applied pressure. Using the traditional method, one can readily establish the pressure at which blood flow through a vessel ceases. However, one cannot determine, for example, whether the blood velocity began to decrease precipitously at a particular applied pressure or whether it decreased gradually throughout the process of applying an external pressure.
It is an object of this invention to provide a method and apparatus for measuring pressure at specific sites in the body in a non-invasive manner.
It is a further object of the invention to provide a method and apparatus for determining the effect of an applied pressure or blood flow across a broad range of applied pressures.
Apparatus and methods are disclosed for non-invasive measurement of blood velocity in otherwise inaccessible regions, and for correlating such measurements with externally applied pressure to detect and/or assess diseases or physiological abnormalities. The blood velocity measurements can be based on the Doppler shift that occurs when an ultrasonic wave is scattered by moving particles within the blood. Since blood vessels have elastic walls, the geometry of the walls, and therefore the flow dynamics, will change in response to elevated in vivo pressure. The change in resistance to blood flow resulting from these pressure induced changes to the wall geometry can provide a measure of intracranial pressure, ophthalmic pressure or various other body conditions that affect blood perfusion. Since wall geometry changes rapidly in response to such changes in pressure, the invention can be used to detect hydrocephalus, glaucoma, retinopathy, papilledema and other physiological abnormalities manifested by pressure changes.
An apparatus, according to the invention, which uses the change in blood flow to measure the pressure driving that flow includes a pressure applicator containing an acoustically transmitting medium through which ultrasonic waves can propagate between the blood vessel or other intracorporeal fluid and an ultrasonic transducer. In one preferred embodiment, the pressure applicator is a bladder filled with an acoustically transparent liquid, such as water, and having a deformable side wall which contacts the skin along a contact area.
The pressure applicator is preferably coupled to a pressure sensor, which measures the pressure applied by the pressure applicator to the surface of the patient, and can be integrated with, or adapted to couple to, an ultrasonic transducer which transmits and receives ultrasonic waves.
Both the pressure applicator and the ultrasonic transducer are in communication with a data processor which uses the received pressure data and ultrasonic signal in the conventional manner to derive the in vivo pressure of the intracorporeal fluid.
Thus, the invention permits an inferred estimation of in vivo pressure based on the compliance of the target tissue and effect of an externally applied pressure on the hemodynamics in the tissue.
These and other features, aspects and advantages of the invention will be better understood with reference to the accompanying drawings in which:
FIG. 1 is a schematic perspective view of an ultrasound probe and pressure measurement apparatus according to the invention.
FIG. 2 shows an apparatus according to the invention resting on the skin covering a fontanelle in a neonatal cranium.
In FIG. 1, a non-invasive pressure measurement apparatus 10 according to the invention includes a hand-held ultrasound probe 12. The geometry of the probe 12 is not critical but can be chosen for ease of manipulation. Various commercially available ultrasound systems can be used to provide an ultrasound probe 12 and to transmit and receive ultrasonic waves, as well as to provide Doppler shift data. For an exemplary discussion of such ultrasound systems, see U.S. Pat. No. 5,640,960 which is incorporated herein by reference.
A pressure applicator 13, which includes a housing 15 and a bladder 16 filled with an acoustically transparent medium 18, is mounted to one end of the ultrasound probe 12. Preferably, the bladder is a flexible structure which deforms in response to the pressure exerted by it bladder on a surface. The acoustically transparent medium can be water, a saline solution, or any other acoustically transparent liquid or gel.
As shown in more detail in FIG. 2, the pressure applicator 13 preferably includes a pressure transducer 19 which is responsive to the pressure exerted by the bladder on a surface. The pressure transducer 19 is coupled to a pressure measurement circuit 22, the output of which becomes an input to a data processor 24. The pressure applicator 13 can be incorporated into a special purpose ultrasound probe or designed as an adapter which is coupled to a conventional probe.
An ultrasonic transducer 14 incorporated into the probe 12 converts electronic signals into ultrasonic waves that are transmitted into the medium 18 and, conversely, converts ultrasonic waves returning back from the medium 18 into electrical signals. The ultrasonic transducer 14 is electrically coupled to both a waveform generator 21 and a waveform detector 20. Alternatively, the functions of the transducer can be performed by one or more separate transmitters or receivers. A housing 15 can surround the bladder 16 to constrain deformation of the bladder when pressure is applied.
In operation, the clinician positions the pressure applicator 13 on the skin over the region in which the blood pressure is to be measured. In FIG. 1, the pressure applicator 13 is shown on the skin 30 covering a fontanelle 36 in a neonatal cranium 32. The clinician applies an external pressure P1 by pressing a contact surface 17 of the pressure applicator 13 against the skin 30. The pressure thus generated by the operator is transmitted, by way of the fluid within the bladder 16, to a pressure transducer 19 which generates an electrical signal representative of the applied external pressure for processing by the pressure measurement circuit 22. Accordingly, a pressure regulation 23 can be used to regulate the pressure applied by the bladder's contact surface or to implement an automated or pre-defined protocol of applied pressure. Such a protocol can be initiated or controlled by data processor 24.
The above procedure can be performed at sites other than the illustrated fontanelle. For example, the apparatus 10 can be placed against a closed eyelid. In such a case, the fluid in the bladder 16 can be acoustically coupled, through the vitreous humor of the eye, to the capillaries feeding the retina for measurement of blood pressure in those capillaries.
The waveform generator 21 transmits an electrical signal to the transducer 14 which then converts it into an ultrasonic wave. The ultrasonic wave propagates through the acoustically transparent medium 18 in the bladder 16 and crosses the skin/bladder interface. As shown in the illustrative example of FIG. 1, the fontanelle 36, over which the bladder rests, provides an aperture through which ultrasonic waves crossing the bladder/skin interface can penetrate the cranium 32 and illuminate a blood vessel 34. Ultrasonic waves crossing the bladder/skin interface propagate through the skin 30 and illuminate blood vessels 34 within the brain 38.
The interaction of the incident ultrasonic radiation with the blood flow within the blood vessel 34 results in a reflected ultrasonic wave having a frequency shifted by an amount representative of the velocity of the blood within the blood vessel. This Doppler shifted ultrasonic wave exits the cranium through the fontanelle 36, crosses the interface between the skin and the bladder, and propagates through the acoustically transparent medium 18 within the bladder 16. The reflected wave impinges on the ultrasonic transducer 14 and thereby generates an electrical signal representative of the reflected wave. This electrical signal is then transmitted to waveform detector 20.
The pressure P1 applied by the operator against the skin 30 affects the blood velocity in the blood vessel 34. Since the reflected ultrasonic wave provides a measure of the blood velocity, this wave is likewise affected by the applied external pressure P1. The measured values of the reflected ultrasonic wave are transmitted to a data processor 24 together with the measured values of external pressure P1. The data processor 24 then uses these two quantities to determine the internal pressure P2 within the cranium 32.
It will thus be seen that the invention efficiently attains the objects set forth above. Since certain changes may be made in the above construction without departing from the scope of the invention, it is intended that all matter contained in the above description or shown in the accompanying drawings be interpreted as illustrative and not limiting. In particular, the illustration of measurements at the fontanelle should be understood to be merely exemplary. The apparatus can be applied to the ophthalmic region to detect retinopathies or applied to the skin to detect venous occlusions. Moreover, it may be preferable, in some applications, to take measurements of the ophthalmic region to detect and/or assess intracranial abnormalities (particularly, in adults whose fontanelle regions have fused).
It is also to be understood that the following claims are intended to cover all generic and specific features of the invention described herein.
Claims (13)
1. An apparatus for ultrasonically evaluating an in vivo pressure, the apparatus comprising:
an ultrasonic transducer for transmitting a first ultrasonic wave to an in vivo target region and detecting a second ultrasonic wave reflected from the in vivo target region, the second ultrasonic wave having a frequency shifted by an amount corresponding to a velocity of blood within a blood vessel in the in vivo target region;
a pressure applicator for applying an external pressure to the target region to alter the blood velocity in the blood vessel;
a pressure sensor for measuring the external pressure applied by the pressure applicator at the target region; and
a data processor in communication with the pressure sensor and the ultrasonic transducer for evaluating an in vivo pressure from the external pressure and the blood velocity in the blood vessel within the in vivo target region as determined from the first and second ultrasonic waves based upon a predetermined correspondence between the external pressure and changes in the blood velocity in the blood vessel within the target region due to the external pressure.
2. The apparatus according to claim 1 wherein the pressure applicator comprises a bladder filled with an acoustically transmissive medium.
3. The apparatus of claim 1 wherein the acoustically transmissive medium comprises a liquid.
4. The apparatus of claim 3 wherein the liquid is water.
5. The apparatus of claim 1 wherein the ultrasonic transducer is adapted to detect a second ultrasonic wave which is a Doppler shifted transformation of the first ultrasonic wave.
6. The apparatus of claim 1 wherein the pressure applicator is adapted for placement against a fontanelle on the neonatal cranium.
7. A method for ultrasonically evaluating an in vivo pressure, the method comprising the steps of:
applying pressure to the target region, thereby developing an external pressure in the target region;
transmitting a first ultrasonic wave into the target region;
detecting a second ultrasonic wave, the second ultrasonic wave generated by an interaction between the first ultrasonic wave and the target region;
measuring the applied external pressure, thereby generating an external pressure measurement;
calculating the in vivo pressure in the target region based on the first and second ultrasonic waves including a shift in frequency of the second ultrasonic wave corresponding to a velocity of blood in a blood vessel in the target region and on the external pressure measurement, wherein there is a predetermined correspondence between the external pressure and changes in the blood velocity due to the external pressure.
8. The method of claim 7 wherein the step of applying an external pressure to the target region comprises the step of placing a bladder against the target region, the bladder being filled with an acoustically transmissive medium.
9. The method of claim 8 wherein the step of measuring the applied external pressure comprises the step of providing a transducer coupled to the bladder.
10. The method according to claim 7 wherein the acoustically transmissive medium is a liquid.
11. The method according to claim 10 wherein the liquid is water.
12. The method according to claim 7 wherein the step of detecting a second ultrasonic wave comprises the step of detecting a Doppler shifted transformation of the first ultrasonic wave.
13. The method according to claim 7 further comprising the step of selecting the target region to be a neonatal cranium and the step of measuring the applied external pressure includes the step of placing the pressure applicator against a fontanelle on the cranium.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/613,648 US6309354B1 (en) | 1998-06-12 | 2000-07-11 | Non-Invasive in vivo pressure measurement |
US10/012,774 US6547734B2 (en) | 1998-06-12 | 2001-10-30 | Non-invasive in vivo pressure measurement |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/097,067 US6086533A (en) | 1998-06-12 | 1998-06-12 | Non-invasive in vivo pressure measurement |
US09/613,648 US6309354B1 (en) | 1998-06-12 | 2000-07-11 | Non-Invasive in vivo pressure measurement |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/097,067 Continuation US6086533A (en) | 1998-06-12 | 1998-06-12 | Non-invasive in vivo pressure measurement |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/012,774 Continuation US6547734B2 (en) | 1998-06-12 | 2001-10-30 | Non-invasive in vivo pressure measurement |
Publications (1)
Publication Number | Publication Date |
---|---|
US6309354B1 true US6309354B1 (en) | 2001-10-30 |
Family
ID=22260783
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/097,067 Expired - Fee Related US6086533A (en) | 1998-06-12 | 1998-06-12 | Non-invasive in vivo pressure measurement |
US09/613,648 Expired - Fee Related US6309354B1 (en) | 1998-06-12 | 2000-07-11 | Non-Invasive in vivo pressure measurement |
US10/012,774 Expired - Lifetime US6547734B2 (en) | 1998-06-12 | 2001-10-30 | Non-invasive in vivo pressure measurement |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/097,067 Expired - Fee Related US6086533A (en) | 1998-06-12 | 1998-06-12 | Non-invasive in vivo pressure measurement |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/012,774 Expired - Lifetime US6547734B2 (en) | 1998-06-12 | 2001-10-30 | Non-invasive in vivo pressure measurement |
Country Status (2)
Country | Link |
---|---|
US (3) | US6086533A (en) |
WO (1) | WO1999063890A1 (en) |
Cited By (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6547734B2 (en) | 1998-06-12 | 2003-04-15 | Children's Medical Center Corporation | Non-invasive in vivo pressure measurement |
US20050050956A1 (en) * | 2003-06-24 | 2005-03-10 | Gysling Daniel L. | Contact-based transducers for characterizing unsteady pressures in pipes |
US20050120799A1 (en) * | 2003-06-24 | 2005-06-09 | Gysling Daniel L. | Contact-based transducers for characterizing unsteady pressures in pipes |
US20080214951A1 (en) * | 2004-02-03 | 2008-09-04 | Neuro Diagnostic Devices, Inc. | Cerebrospinal Fluid Evaluation Systems |
US7520862B2 (en) | 2004-02-03 | 2009-04-21 | Neuro Diagnostic Devices, Inc. | Cerebral spinal fluid shunt evaluation system |
US20090287084A1 (en) * | 2008-05-15 | 2009-11-19 | Arminas Ragauskas | Method and Apparatus for Continuously Monitoring Intracranial Pressure |
US10617388B2 (en) | 2016-01-05 | 2020-04-14 | Neural Analytics, Inc. | Integrated probe structure |
US10709417B2 (en) | 2016-01-05 | 2020-07-14 | Neural Analytics, Inc. | Systems and methods for detecting neurological conditions |
US11000258B2 (en) | 2015-09-08 | 2021-05-11 | Kurume University | Noninvesive arteriovenous pressure measurement device and arteriovenous pressure measurement method using the measurement device |
US11090026B2 (en) | 2016-01-05 | 2021-08-17 | Novasignal Corp. | Systems and methods for determining clinical indications |
US11207054B2 (en) | 2015-06-19 | 2021-12-28 | Novasignal Corp. | Transcranial doppler probe |
Families Citing this family (46)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6050943A (en) | 1997-10-14 | 2000-04-18 | Guided Therapy Systems, Inc. | Imaging, therapy, and temperature monitoring ultrasonic system |
EP1085835A4 (en) * | 1998-06-19 | 2002-10-30 | Uab Research Foundation | Oximetric tonometer with intracranial pressure monitoring capability |
EP1248556A2 (en) | 2000-01-07 | 2002-10-16 | Rice Creek Medical, L.L.C. | Non-invasive method and apparatus for monitoring intracranial pressure |
US6702743B2 (en) * | 2000-05-26 | 2004-03-09 | Inta-Medics, Ltd. | Ultrasound apparatus and method for tissue resonance analysis |
US6328694B1 (en) * | 2000-05-26 | 2001-12-11 | Inta-Medics, Ltd | Ultrasound apparatus and method for tissue resonance analysis |
US7629890B2 (en) | 2003-12-04 | 2009-12-08 | Hoana Medical, Inc. | System and methods for intelligent medical vigilance with bed exit detection |
US20060079773A1 (en) * | 2000-11-28 | 2006-04-13 | Allez Physionix Limited | Systems and methods for making non-invasive physiological assessments by detecting induced acoustic emissions |
US7547283B2 (en) * | 2000-11-28 | 2009-06-16 | Physiosonics, Inc. | Methods for determining intracranial pressure non-invasively |
JP2004520870A (en) | 2000-11-28 | 2004-07-15 | アレズ フィジオニックス リミテッド | Non-invasive physiological evaluation system and method |
GB0121984D0 (en) * | 2001-09-11 | 2001-10-31 | Isis Innovation | Method and apparatus for ultrasound examination |
US7491173B2 (en) * | 2001-10-10 | 2009-02-17 | Team Medical, Llc | Method and system for obtaining dimension related information for a flow channel |
US7131945B2 (en) | 2002-10-16 | 2006-11-07 | California Institute Of Technology | Optically powered and optically data-transmitting wireless intraocular pressure sensor device |
US7122007B2 (en) * | 2003-05-12 | 2006-10-17 | Caritas St. Elizabeth Medical Center Of Boston, Inc. | Methods of and systems and devices for assessing intracranial pressure non-invasively |
EP1633234A4 (en) | 2003-06-03 | 2009-05-13 | Physiosonics Inc | Systems and methods for determining intracranial pressure non-invasively and acoustic transducer assemblies for use in such systems |
US7854701B2 (en) * | 2003-07-24 | 2010-12-21 | Stergios Stergiopoulos | Non-invasive monitoring of intracranial dynamic effects and brain density fluctuations |
US7374539B2 (en) * | 2003-09-02 | 2008-05-20 | University Of Utah Research Foundation | Method and apparatus for predicting material hypertension during pregnancy using coherence analysis of material and fetal blood velocity waveforms |
AU2004296792B2 (en) * | 2003-12-04 | 2012-04-19 | Hoana Medical, Inc. | Intelligent medical vigilance system |
US7393325B2 (en) | 2004-09-16 | 2008-07-01 | Guided Therapy Systems, L.L.C. | Method and system for ultrasound treatment with a multi-directional transducer |
US9011336B2 (en) | 2004-09-16 | 2015-04-21 | Guided Therapy Systems, Llc | Method and system for combined energy therapy profile |
US7824348B2 (en) | 2004-09-16 | 2010-11-02 | Guided Therapy Systems, L.L.C. | System and method for variable depth ultrasound treatment |
US7758524B2 (en) | 2004-10-06 | 2010-07-20 | Guided Therapy Systems, L.L.C. | Method and system for ultra-high frequency ultrasound treatment |
WO2007069155A1 (en) * | 2005-12-14 | 2007-06-21 | Koninklijke Philips Electronics N.V. | Doppler detection of pulsatile blood flow |
US8109880B1 (en) | 2006-12-26 | 2012-02-07 | Osvaldas Pranevicius | Noninvasive method to measure intracranial and effective cerebral outflow pressure |
CN100548212C (en) * | 2007-01-18 | 2009-10-14 | 北京大学人民医院 | Noninvasive intracranial pressure monitoring equipment |
TWI526233B (en) | 2007-05-07 | 2016-03-21 | 指導治療系統股份有限公司 | Methods and systems for modulating medicants using acoustic energy |
US20150174388A1 (en) | 2007-05-07 | 2015-06-25 | Guided Therapy Systems, Llc | Methods and Systems for Ultrasound Assisted Delivery of a Medicant to Tissue |
WO2009141758A1 (en) * | 2008-05-19 | 2009-11-26 | Koninklijke Philips Electronics N.V. | Perfusion regulation device |
DE102008030942A1 (en) | 2008-07-02 | 2010-01-07 | Christoph Miethke Gmbh & Co Kg | Cerebrospinal fluid drainage |
DE102008061018B3 (en) | 2008-12-08 | 2010-07-08 | Charité - Universitätsmedizin Berlin | Measuring device and method for non-invasive long-term measurement of blood pressure |
US8277385B2 (en) | 2009-02-04 | 2012-10-02 | Advanced Brain Monitoring, Inc. | Method and apparatus for non-invasive assessment of hemodynamic and functional state of the brain |
US8206303B2 (en) * | 2009-08-21 | 2012-06-26 | Uab Vittamed | Apparatus and method for simulating arterial blood flow under various pressure conditions |
US8715186B2 (en) | 2009-11-24 | 2014-05-06 | Guided Therapy Systems, Llc | Methods and systems for generating thermal bubbles for improved ultrasound imaging and therapy |
US8961420B2 (en) | 2010-04-01 | 2015-02-24 | Siemens Medical Solutions Usa, Inc. | System for cardiac condition detection and characterization |
US10183182B2 (en) | 2010-08-02 | 2019-01-22 | Guided Therapy Systems, Llc | Methods and systems for treating plantar fascia |
US9504446B2 (en) | 2010-08-02 | 2016-11-29 | Guided Therapy Systems, Llc | Systems and methods for coupling an ultrasound source to tissue |
US8858471B2 (en) | 2011-07-10 | 2014-10-14 | Guided Therapy Systems, Llc | Methods and systems for ultrasound treatment |
KR20190080967A (en) | 2011-07-11 | 2019-07-08 | 가이디드 테라피 시스템스, 엘.엘.씨. | Systems and methods for coupling an ultrasound source to tissue |
US9263663B2 (en) | 2012-04-13 | 2016-02-16 | Ardent Sound, Inc. | Method of making thick film transducer arrays |
EP2710961B1 (en) | 2012-09-24 | 2019-08-07 | Veinpress GmbH | Pressure measurement device for pressure measurement of a vein or an organ and for combination with an ultrasound measuring unit, and system and method for venous/organ pressure measurement |
US10561862B2 (en) | 2013-03-15 | 2020-02-18 | Guided Therapy Systems, Llc | Ultrasound treatment device and methods of use |
WO2014145926A2 (en) * | 2013-03-15 | 2014-09-18 | Ardent Sound, Inc. | Liquid-filled acoustic probe system with reservoir and loss detection means |
EP3634564B1 (en) * | 2017-06-07 | 2023-11-22 | Frederick H. Sklar | Apparatus for minimally-invasive prevention and treatment of hydrocephalus |
WO2019234765A1 (en) * | 2018-06-07 | 2019-12-12 | Healthcare Technology Innovation Centre | Multi-modal ultrasound probe for calibration-free cuff-less evaluation of blood pressure |
RU194365U1 (en) * | 2019-09-23 | 2019-12-06 | Общество с ограниченной ответственностью (ООО) "АЛЬТОНИКА" | Ultrasonic handheld transducer for remote blood flow assessment |
US10709345B1 (en) | 2019-11-26 | 2020-07-14 | David Michaeli | Method and apparatus for noninvasive absolute (mean) intracranial pressure (A-ICP) measurement and/or monitoring |
DE102021109202B3 (en) | 2021-04-13 | 2022-08-18 | Richard Martin Sellei | Method for measuring an internal pressure of a compartment |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4127114A (en) * | 1976-08-30 | 1978-11-28 | Carba S.A. | Apparatus for the automatic measurement of the arterial pressure of a patient |
US5895357A (en) * | 1996-01-29 | 1999-04-20 | Aloka Co., Ltd. | Bone assessment apparatus |
US5951477A (en) * | 1997-09-11 | 1999-09-14 | Uab Vittamed | Method and apparatus for determining the pressure inside the brain |
US6086533A (en) * | 1998-06-12 | 2000-07-11 | Children's Medical Center Corporation | Non-invasive in vivo pressure measurement |
Family Cites Families (22)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4033178A (en) * | 1976-04-23 | 1977-07-05 | The Babcock & Wilcox Company | Fluid coupled test probe |
US4203451A (en) * | 1978-03-17 | 1980-05-20 | Panico Joseph J | Cardiovascular analysis, method and apparatus |
US4237901A (en) * | 1978-08-30 | 1980-12-09 | Picker Corporation | Low and constant pressure transducer probe for ultrasonic diagnostic system |
EP0148221A1 (en) * | 1983-07-01 | 1985-07-17 | SKRABAL, Falko | Sphygmomanometer |
US4566462A (en) * | 1983-11-21 | 1986-01-28 | School Of Medicine Texas Tech. Univ. Health Servcs. Ctr. | Venous pressure measuring method and apparatus |
FR2602663A1 (en) * | 1986-08-14 | 1988-02-19 | Kedra Antoni | Probe and apparatus for measuring blood pressure, in particular in the ophthalmic artery |
FR2617394B1 (en) * | 1987-07-03 | 1994-07-29 | Boutin Gerard | DEVICE FOR MEASURING BLOOD PRESSURE IN A SURFACE ARTERY |
US4995401A (en) * | 1988-02-26 | 1991-02-26 | Board Of Regents, The University Of Texas System | Device for measuring anterior fontanelle pressure |
US5072736A (en) * | 1990-01-19 | 1991-12-17 | Nihon Kohden Corporation | Non-invasive automatic blood pressure measuring apparatus |
GB9213220D0 (en) * | 1992-06-22 | 1992-08-05 | Langton Christian M | Ultrasound bone analyser |
GB9215231D0 (en) * | 1992-07-17 | 1992-09-02 | Skidmore Robert | Flowmeters |
DE69333503T2 (en) * | 1992-09-21 | 2004-11-18 | Institut National De La Santé Et De La Recherche Médicale (Inserm) | INTRACORPORAL PROBE FOR DETERMINING THE SPEED OF A LIQUID, IN PARTICULAR THE FLOW THROUGH THE AORTA |
GB9312962D0 (en) * | 1993-06-23 | 1993-08-04 | Akinyemi Samuel N O | An indirect pulse pressure manometer |
JPH07241288A (en) * | 1994-03-04 | 1995-09-19 | Hitachi Ltd | Ultrasonic device |
US5503156A (en) * | 1994-03-11 | 1996-04-02 | Millar Instruments, Inc. | Noninvasive pulse transducer for simultaneously measuring pulse pressure and velocity |
US5454372A (en) * | 1994-06-17 | 1995-10-03 | Siemens Medical Systems, Inc. | Angle independent doppler in ultrasound imaging |
US5701898A (en) * | 1994-09-02 | 1997-12-30 | The United States Of America As Represented By The Department Of Health And Human Services | Method and system for Doppler ultrasound measurement of blood flow |
JP2840040B2 (en) * | 1994-12-22 | 1998-12-24 | アロカ株式会社 | Measurement method of sound velocity in tissue |
US5487389A (en) * | 1994-12-29 | 1996-01-30 | Siemens Medical Systems, Inc. | Ultrasonic Doppler imager having an adaptive tissue rejection filter with enhanced tissue motion sensitivity |
US5640960A (en) * | 1995-04-18 | 1997-06-24 | Imex Medical Systems, Inc. | Hand-held, battery operated, doppler ultrasound medical diagnostic device with cordless probe |
JP3865800B2 (en) * | 1995-05-15 | 2007-01-10 | 株式会社東芝 | Ultrasonic diagnostic equipment |
US5738097A (en) * | 1996-11-08 | 1998-04-14 | Diagnostics Ultrasound Corporation | Vector Doppler system for stroke screening |
-
1998
- 1998-06-12 US US09/097,067 patent/US6086533A/en not_active Expired - Fee Related
-
1999
- 1999-06-11 WO PCT/US1999/013349 patent/WO1999063890A1/en active Application Filing
-
2000
- 2000-07-11 US US09/613,648 patent/US6309354B1/en not_active Expired - Fee Related
-
2001
- 2001-10-30 US US10/012,774 patent/US6547734B2/en not_active Expired - Lifetime
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4127114A (en) * | 1976-08-30 | 1978-11-28 | Carba S.A. | Apparatus for the automatic measurement of the arterial pressure of a patient |
US5895357A (en) * | 1996-01-29 | 1999-04-20 | Aloka Co., Ltd. | Bone assessment apparatus |
US5951477A (en) * | 1997-09-11 | 1999-09-14 | Uab Vittamed | Method and apparatus for determining the pressure inside the brain |
US6086533A (en) * | 1998-06-12 | 2000-07-11 | Children's Medical Center Corporation | Non-invasive in vivo pressure measurement |
Cited By (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6547734B2 (en) | 1998-06-12 | 2003-04-15 | Children's Medical Center Corporation | Non-invasive in vivo pressure measurement |
US20050050956A1 (en) * | 2003-06-24 | 2005-03-10 | Gysling Daniel L. | Contact-based transducers for characterizing unsteady pressures in pipes |
US20050120799A1 (en) * | 2003-06-24 | 2005-06-09 | Gysling Daniel L. | Contact-based transducers for characterizing unsteady pressures in pipes |
US7197938B2 (en) * | 2003-06-24 | 2007-04-03 | Cidra Corporation | Contact-based transducers for characterizing unsteady pressures in pipes |
US20080214951A1 (en) * | 2004-02-03 | 2008-09-04 | Neuro Diagnostic Devices, Inc. | Cerebrospinal Fluid Evaluation Systems |
US7520862B2 (en) | 2004-02-03 | 2009-04-21 | Neuro Diagnostic Devices, Inc. | Cerebral spinal fluid shunt evaluation system |
US8926515B2 (en) * | 2008-05-15 | 2015-01-06 | Uab Vittamed | Method and apparatus for continuously monitoring intracranial pressure |
US20120238885A1 (en) * | 2008-05-15 | 2012-09-20 | Arminas Ragauskas | Method and apparatus for continuously monitoring intracranial pressure |
US20090287084A1 (en) * | 2008-05-15 | 2009-11-19 | Arminas Ragauskas | Method and Apparatus for Continuously Monitoring Intracranial Pressure |
US9168023B2 (en) * | 2008-05-15 | 2015-10-27 | Uab Vittamed | Method and apparatus for continuously monitoring intracranial pressure |
US11207054B2 (en) | 2015-06-19 | 2021-12-28 | Novasignal Corp. | Transcranial doppler probe |
US11000258B2 (en) | 2015-09-08 | 2021-05-11 | Kurume University | Noninvesive arteriovenous pressure measurement device and arteriovenous pressure measurement method using the measurement device |
US10617388B2 (en) | 2016-01-05 | 2020-04-14 | Neural Analytics, Inc. | Integrated probe structure |
US10709417B2 (en) | 2016-01-05 | 2020-07-14 | Neural Analytics, Inc. | Systems and methods for detecting neurological conditions |
US11090026B2 (en) | 2016-01-05 | 2021-08-17 | Novasignal Corp. | Systems and methods for determining clinical indications |
US11452500B2 (en) | 2016-01-05 | 2022-09-27 | Novasignal Corp. | Integrated probe structure |
US11589836B2 (en) | 2016-01-05 | 2023-02-28 | Novasignal Corp. | Systems and methods for detecting neurological conditions |
Also Published As
Publication number | Publication date |
---|---|
US6086533A (en) | 2000-07-11 |
US6547734B2 (en) | 2003-04-15 |
US20020052550A1 (en) | 2002-05-02 |
WO1999063890A1 (en) | 1999-12-16 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6309354B1 (en) | Non-Invasive in vivo pressure measurement | |
RU2218090C2 (en) | Method and device for determining intracerebral pressure | |
US5503156A (en) | Noninvasive pulse transducer for simultaneously measuring pulse pressure and velocity | |
US6773407B2 (en) | Non-invasive method of determining absolute intracranial pressure | |
US20100298702A1 (en) | Needle insertion systems and methods | |
US6740048B2 (en) | Non-invasive method of determining diastolic intracranial pressure | |
WO2001054584A1 (en) | Ultrasonic apparatus and technique to measure changes in intracranial pressure | |
US20070270720A1 (en) | Noninvasive physiologic pressure measurement | |
EP2606827B1 (en) | Cuff with ultrasonically transmissive portion and method of observing a tissue under pressure by using the same | |
JPH0363059A (en) | Blood flow measurement using self-irrigation catheter for blood vessel formation and its device | |
US6387051B1 (en) | Method and apparatus for non-invasively deriving and indicating of dynamic characteristics of the human and animal intracranial media | |
US4566462A (en) | Venous pressure measuring method and apparatus | |
US11690591B2 (en) | Apparatus and methods for detecting increase in brain swelling and/or shifting | |
WO2002041750A2 (en) | Non-invasive cerebral spinal fluid pressure monitor apparatus and method | |
JP4405398B2 (en) | Extravasation detector | |
CN216702565U (en) | Wearable visual ultrasonic noninvasive monitoring instrument | |
KR102114350B1 (en) | Non-invasive Apparatus for measuring intracranial pressure | |
CN113440165A (en) | Wearable visual ultrasonic non-invasive monitoring equipment | |
KR101903296B1 (en) | Apparatus for monitoring pulmonary edema | |
US10360816B2 (en) | System and method for simulating fetal heart rate for noninvasive intra-partum fetal monitoring | |
JPH0347851B2 (en) | ||
O'Leary | Vascular ultrasonography | |
JP2005021347A (en) | Sphygmomanometer and method for measuring blood pressure | |
EP4327733A1 (en) | Lumen design within intravenous tube to transmit blood pressure wave for invasive blood pressure monitoring | |
CN113457005B (en) | Bubble detection method, electronic device, readable storage medium, and blood pump system |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
FPAY | Fee payment |
Year of fee payment: 4 |
|
FPAY | Fee payment |
Year of fee payment: 8 |
|
REMI | Maintenance fee reminder mailed | ||
LAPS | Lapse for failure to pay maintenance fees | ||
STCH | Information on status: patent discontinuation |
Free format text: PATENT EXPIRED DUE TO NONPAYMENT OF MAINTENANCE FEES UNDER 37 CFR 1.362 |
|
FP | Lapsed due to failure to pay maintenance fee |
Effective date: 20131030 |